Breathing machine output gas monitoring method, system and device and storage medium

Abstract

The invention discloses a breathing machine output gas monitoring method, system and device and a storage medium. The breathing machine output gas monitoring method comprises the steps that airway pressure information, gas flow information and oxygen concentration information of breathing pipeline gas are obtained; determining tidal volume, respiratory rate and inspiration and expiration ratio according to the gas flow information; performing air leakage compensation on the tidal volume according to the airway pressure information to obtain a real tidal volume; the airway pressure information, the inspiration and expiration ratio, the real tidal volume, the respiratory rate and the oxygen concentration information are displayed. The breathing machine output gas monitoring comprehensiveness and accuracy are improved, and the breathing machine output gas monitoring method can be widely applied to the technical field of breathing machines.

Description

Technical Field

[0001] The present invention relates to the technical field of ventilators, and in particular to a method, system, device and storage medium for monitoring output gas of a ventilator. Background Art

[0002] Existing ventilator output gas monitoring devices mainly rely on a single or a small number of sensors for data collection, which are usually limited to monitoring specific parameters such as gas flow rate or oxygen concentration, and often lack the ability to monitor more complex physiological parameters such as blood oxygen saturation and heart rate. Although some advanced systems have multi-sensor fusion functions, they are mostly integrated into high-end equipment, which are expensive, large in size, not easy to carry and use, and lack open interfaces, making it difficult to achieve secondary development and innovation of basic equipment, affecting the comprehensiveness and accuracy of ventilator output gas monitoring. Summary of the invention

[0003] The purpose of the present invention is to solve one of the technical problems existing in the prior art to at least a certain extent.

[0004] To this end, an object of an embodiment of the present invention is to provide a method for monitoring output gas of a ventilator, which improves the comprehensiveness and accuracy of monitoring output gas of the ventilator.

[0005] Another object of an embodiment of the present invention is to provide a ventilator output gas monitoring system.

[0006] In order to achieve the above technical objectives, the technical solutions adopted by the embodiments of the present invention include:

[0007] In a first aspect, an embodiment of the present invention provides a method for monitoring output gas of a ventilator, comprising the following steps:

[0008] Obtaining airway pressure information, gas flow information and oxygen concentration information of the breathing tube gas;

[0009] Determine tidal volume, respiratory rate and inspiration-expiration ratio according to the gas flow information;

[0010] Perform leakage compensation on the tidal volume according to the airway pressure information to obtain a real tidal volume;

[0011] The airway pressure information, the inspiration-expiration ratio, the true tidal volume, the respiratory rate and the oxygen concentration information are displayed.

[0012] Further, in one embodiment of the present invention, the obtaining of airway pressure information, gas flow information and oxygen concentration information of the breathing duct gas specifically includes:

[0013] Acquiring the airway pressure information of the breathing duct gas through a pressure sensor arranged in the breathing duct;

[0014] Acquiring the gas flow information of the gas in the breathing duct by means of a differential pressure flow sensor arranged in the breathing duct;

[0015] The oxygen concentration information of the breathing duct gas is obtained through an oxygen sensor arranged in the breathing duct.

[0016] Further, in one embodiment of the present invention, the tidal volume is determined by the following steps:

[0017] Determine whether the current breathing state is an inhalation state or an exhalation state according to the current gas flow information;

[0018] When the current breathing state is the inhalation state, the current inhalation volume is determined according to the gas flow information, and the current inhalation total volume is determined according to the sum of the current inhalation volume and the previous inhalation total volume;

[0019] When the current breathing state changes from the inhalation state to the exhalation state, the tidal volume is determined according to the quotient of the current inhalation total volume and the current breathing number, and the current inhalation total volume and the current breathing number are set to 0.

[0020] Further, in one embodiment of the present invention, the respiratory rate and the inhalation-exhalation ratio are determined by the following steps:

[0021] Determine whether the current breathing state is an inhalation state or an exhalation state according to the current gas flow information;

[0022] When the current breathing state is the inhalation state, the current inhalation time is determined according to the gas flow information, and the current total inhalation time is determined according to the sum of the current inhalation time and the total amount of the previous inhalation time;

[0023] When the current breathing state is the exhalation state, the current exhalation time is determined according to the gas flow information, and the current total exhalation time is determined according to the sum of the current exhalation time and the total exhalation time of the previous time;

[0024] When the current breathing state changes from an inhalation state to an exhalation state, the inhalation-exhalation ratio is determined according to the quotient of the current total inhalation time and the current total exhalation time, the average breathing time is determined according to the current total inhalation time, the current total exhalation time and the current number of breaths, and then the breathing frequency is determined according to the average breathing time, and the current total inhalation time, the current total exhalation time and the current number of breaths are set to 0.

[0025] Further, in one embodiment of the present invention, the leak compensation of the tidal volume according to the airway pressure information to obtain the real tidal volume specifically includes:

[0026] Obtaining a leakage flow-airway pressure mapping table pre-calibrated by experiments;

[0027] According to the airway pressure information, query the air leakage flow-airway pressure mapping table to obtain the current air leakage flow;

[0028] The actual tidal volume is determined according to the sum of the current leakage flow and the tidal volume.

[0029] Furthermore, in one embodiment of the present invention, the ventilator output gas monitoring method further includes a low ventilation warning step, which specifically includes:

[0030] Determine a first maximum airflow value and a first minimum airflow value within a preset time period according to the gas flow information, and determine a basic tidal volume according to a difference between the first maximum airflow value and the first minimum airflow value;

[0031] determining a second maximum airflow value and a second minimum airflow value of a current period according to the gas flow information, and determining a current tidal volume according to a difference between the second maximum airflow value and the second minimum airflow value;

[0032] When the current tidal volume is less than 30 percent of the basic tidal volume, a low ventilation alarm is issued.

[0033] Furthermore, in one embodiment of the present invention, the ventilator output gas monitoring method further includes the following steps:

[0034] Obtain the user's blood oxygen saturation and heart rate through the blood oxygen and heart rate monitoring module;

[0035] When the blood oxygen saturation is detected to be lower than a preset first threshold for a preset number of times within a preset breathing cycle, a hypoglycemia alarm is issued.

[0036] In a second aspect, an embodiment of the present invention provides a ventilator output gas monitoring system, comprising:

[0037] An information acquisition module, used to obtain airway pressure information, gas flow information and oxygen concentration information of the breathing duct gas;

[0038] An information processing module, used to determine tidal volume, respiratory rate and inspiration-expiration ratio according to the gas flow information;

[0039] A leakage compensation module, used for performing leakage compensation on the tidal volume according to the airway pressure information to obtain a real tidal volume;

[0040] An information display module is used to display the airway pressure information, the inspiration-expiration ratio, the real tidal volume, the respiratory rate and the oxygen concentration information.

[0041] In a third aspect, an embodiment of the present invention provides a ventilator output gas monitoring device, comprising:

[0042] at least one processor;

[0043] at least one memory for storing at least one program;

[0044] When the at least one program is executed by the at least one processor, the at least one processor implements the above-mentioned ventilator output gas monitoring method.

[0045] In a fourth aspect, an embodiment of the present invention further provides a computer-readable storage medium, in which a program executable by a processor is stored. When the program executable by the processor is executed by the processor, it is used to execute the above-mentioned method for monitoring the output gas of a ventilator.

[0046] The advantages and beneficial effects of the present invention will be partly given in the following description, partly become apparent from the following description, or be understood through the practice of the present invention:

[0047] The embodiment of the present invention obtains airway pressure information, gas flow information and oxygen concentration information of the breathing duct gas, determines the tidal volume, respiratory rate and inspiration-expiration ratio according to the gas flow information, performs leakage compensation on the tidal volume according to the airway pressure information, obtains the real tidal volume, displays the airway pressure information, inspiration-expiration ratio, real tidal volume, respiratory rate and oxygen concentration information, and improves the comprehensiveness and accuracy of ventilator output gas monitoring. BRIEF DESCRIPTION OF THE DRAWINGS

[0048] In order to more clearly illustrate the technical solution in the embodiments of the present invention, the following introduction is made to the drawings required for use in the embodiments of the present invention. It should be understood that the drawings introduced below are only for the convenience of clearly describing some embodiments of the technical solution of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative work.

[0049] Figure 1 A flow chart of the steps of a method for monitoring output gas of a ventilator provided by an embodiment of the present invention;

[0050] Figure 2 A schematic diagram of hardware equipment for a ventilator output gas monitoring method provided by an embodiment of the present invention;

[0051] Figure 3 A signal processing schematic diagram of a ventilator output gas monitoring method provided by an embodiment of the present invention;

[0052] Figure 4 A structural block diagram of a ventilator output gas monitoring system provided by an embodiment of the present invention;

[0053] Figure 5 A structural block diagram of a ventilator output gas monitoring device provided in an embodiment of the present invention. DETAILED DESCRIPTION

[0054] The embodiments of the present invention are described in detail below, and examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present invention, and are not to be construed as limitations of the present invention. For the step numbers in the following embodiments, they are only provided for the convenience of explanation, and the order between the steps is not limited in any way, and the execution order of each step in the embodiment can be adaptively adjusted according to the understanding of those skilled in the art.

[0055] In the description of the present invention, the meaning of "a plurality" is two or more than two. If there is a description of "a first" or "a second", it is only used for the purpose of distinguishing technical features, and cannot be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features or implicitly indicating the order of the indicated technical features. In addition, unless otherwise defined, all technical and scientific terms used in this document have the same meaning as those commonly understood by those skilled in the art.

[0056] Reference Figure 1 The embodiment of the present invention provides a method for monitoring the output gas of a ventilator, which specifically includes the following steps:

[0057] S101, obtaining airway pressure information, gas flow information, and oxygen concentration information of the breathing duct gas;

[0058] S102, determining tidal volume, respiratory rate, and inspiration-expiration ratio according to gas flow information;

[0059] S103, performing air leakage compensation on the tidal volume according to the airway pressure information to obtain a real tidal volume;

[0060] S104, displaying airway pressure information, inspiration-expiration ratio, true tidal volume, respiratory rate and oxygen concentration information.

[0061] The embodiment of the present invention obtains airway pressure information, gas flow information and oxygen concentration information of the breathing duct gas, determines the tidal volume, respiratory rate and inspiration-expiration ratio according to the gas flow information, performs leakage compensation on the tidal volume according to the airway pressure information, obtains the real tidal volume, displays the airway pressure information, inspiration-expiration ratio, real tidal volume, respiratory rate and oxygen concentration information, and improves the comprehensiveness and accuracy of ventilator output gas monitoring.

[0062] The existing ventilator output gas monitoring solutions have the following disadvantages:

[0063] 1) Limited monitoring parameters: Many existing devices only monitor a single or a small number of gas parameters and lack monitoring of other important physiological parameters (such as blood oxygen saturation and heart rate), and cannot provide comprehensive diagnostic support.

[0064] 2) Closed system: lack of open interfaces makes it difficult to conduct secondary development based on the device.

[0065] 3) The equipment is large and has poor portability: Existing monitoring systems are often large in size and have poor portability, making them difficult to use in mobile environments or emergency situations.

[0066] 4) High power consumption: not suitable for long-term continuous use.

[0067] 5) Insufficient data processing capabilities: Some devices lack real-time data analysis capabilities and cannot respond quickly to changes in patient status.

[0068] 6) Insufficient accuracy: Due to the use of simple sensors, the existing system may not have high enough accuracy and stability in monitoring parameters such as gas flow rate, pressure and oxygen concentration.

[0069] The present invention monitors the output gas of a ventilator based on an STM32 microcontroller and multiple sensors, thereby realizing real-time and accurate monitoring and analysis of the output gas of the ventilator, solving the problems of limited monitoring parameters, poor portability, high power consumption, insufficient data processing capability and insufficient monitoring accuracy in the prior art, and further simplifying the process of secondary development. The present invention is a device capable of real-time and accurate monitoring of multiple parameters (such as oxygen concentration, gas flow rate, gas pressure, etc.) of the output gas of a ventilator and calculating key indicators such as tidal volume and respiratory frequency; the monitoring functions of physiological parameters such as blood oxygen saturation and heart rate are integrated to provide a comprehensive patient status assessment; the STM32 microcontroller is used to realize efficient and stable data processing, and long-term continuous monitoring is realized with low power consumption; the leakage compensation strategy is used to calculate the corresponding leakage flow in real time according to the pressure value, and the real flow of breathing is calculated to realize high-precision tidal volume calculation.

[0070] As an optional implementation, obtaining airway pressure information, gas flow information, and oxygen concentration information of the breathing duct gas specifically includes:

[0071] Acquiring airway pressure information of the breathing duct gas through a pressure sensor arranged in the breathing duct;

[0072] The gas flow information of the gas in the breathing duct is obtained by using a differential pressure flow sensor arranged in the breathing duct;

[0073] The oxygen concentration information of the breathing duct gas is obtained through the oxygen sensor installed in the breathing duct.

[0074] The ventilator output gas monitoring solution of the present invention adopts a data acquisition module based on a multi-sensor, a parameter calculation module based on an STM32 core control board, and a display module based on an LCD display screen. Figure 2 The figure shows a schematic diagram of the hardware equipment of the ventilator output gas monitoring method provided by an embodiment of the present invention. After the gas in the respiratory duct flows through the pressure sensor 2, the differential pressure flow sensor 3, and the oxygen concentration sensor 4 through the pipeline, the airway pressure, gas flow, oxygen concentration, inspiratory-expiratory ratio, and tidal volume are calculated by the core control board 1. In addition, during measurement, the finger touches the blood oxygen and heart rate module 5, and the blood oxygen saturation and heart rate are obtained through a series of processing and calculation. After obtaining the key respiratory parameters such as airway pressure, gas flow, oxygen concentration, inspiratory-expiratory ratio, tidal volume, respiratory frequency, blood oxygen saturation, and heart rate, the parameters are displayed using the LCD display 6.

[0075] like Figure 3 The figure shows a signal processing schematic diagram of the ventilator output gas monitoring method provided by an embodiment of the present invention, and each task is described in detail as follows:

[0076] 1. Data collection:

[0077] Airway pressure sampling: GZP6859A pressure sensor is used to sample airway pressure, with 3.0-5.5V power supply, and optional standard voltage output or proportional voltage output. In order to complete the detection of airway pressure in the range of 1-20cmH2O, it is known that 1kPa≈10.2cmH2O, so a model with a pressure range of 0-4kPa is selected. Since the output signal range of this airway pressure sampling circuit is 0-5V, which exceeds the AD reference voltage, it is necessary to scale down the voltage signal and send it to the AD conversion pin of the microprocessor for AD conversion.

[0078] Gas flow detection: The differential pressure sensor SDP816-500PA is used for gas flow detection. This sensor can measure flow with excellent accuracy, and has the advantages of high-precision temperature compensation, accurate measurement and wide application range. Since the output signal range of this gas flow detection circuit is 0-5V, which exceeds the AD reference voltage, the voltage signal needs to be scaled down and sent to the AD conversion pin of the microprocessor for AD conversion.

[0079] Oxygen concentration detection: The oxygen concentration detection circuit uses the OCS-3FL ultrasonic oxygen sensor. It uses the ultrasonic principle to detect the oxygen concentration and flow rate in the gas output by the oxygen concentrator, and achieves oxygen concentration detection in the range of 21%-95.6% and an accuracy of 0.1%. The acquisition of oxygen concentration parameters uses the UART1 of STM32 for serial communication. After UART3 receives the data, since the serial interrupt priority is set higher than the timer interrupt, it can enter the serial interrupt service subroutine to calculate the current oxygen concentration.

[0080] Blood oxygen and heart rate measurement: The MAX30102 module produced by Maxim Semiconductor is used to monitor blood oxygen saturation and heart rate. During measurement, the finger touches the photoelectric sensor of MAX30102 (i.e., blood oxygen and heart rate module 5), collects the reflected signal of the finger blood, amplifies the transmitted signal, performs analog-to-digital conversion, and outputs the data to the WIFI module controller through the I2C bus. The controller first eliminates the DC offset of the infrared and red light signals and performs baseline leveling; then calculates the amplitude and correlation of the signal; performs periodic detection based on the correlation of the signal, etc., to determine whether the signal is valid; finally, calculates blood oxygen saturation and heart rate based on the signal characteristics.

[0081] 2. Parameter calculation

[0082] The pressure and flow are based on a sampling rate of 100, using a timer of 10ms. After entering the interrupt, the STM32 DMA+AD multi-channel data transfer method obtains the sensor parameters. After AD conversion, the output voltage values ​​of the pressure sensor and flow sensor are obtained. The current pressure and flow values ​​can be obtained by substituting them into the fitted pressure-voltage and flow-voltage formulas.

[0083] Based on the flow value, the three respiratory gas parameters of tidal volume, respiratory rate and inspiration-expiration ratio can be calculated.

[0084] 3. LCD display

[0085] The color screen display module of this system uses the 2.4-inch SPI Module MSP2402. This LCD module can work under 3V3 voltage and can realize color screen character strings and Chinese characters display after proper initialization.

[0086] As a further optional embodiment, the tidal volume is determined by the following steps:

[0087] Determine whether the current breathing state is an inhalation state or an exhalation state according to the current gas flow information;

[0088] When the current breathing state is the inhalation state, the current inhalation volume is determined according to the gas flow information, and the current inhalation volume is determined according to the sum of the current inhalation volume and the previous inhalation volume;

[0089] When the current breathing state changes from the inhalation state to the exhalation state, the tidal volume is determined according to the quotient of the current inhalation total volume and the current respiratory number, and the current inhalation total volume and the current respiratory number are set to 0.

[0090] Specifically, each time the timer interrupt is entered to sample the flow, the current breathing state is determined according to the positive and negative values ​​of the flow. A positive flow is set to indicate the inhalation state, and a negative flow is set to indicate the exhalation state. If the current state is in the inhalation state and there is no change in the breathing state, the total amount of inhalation is calculated, that is, the total amount of inhalation = this inhalation volume + the total amount of the previous inhalation, and the current exhalation volume = flow / 60s / sampling frequency*1000; if the current breathing state is converted from inhalation to exhalation, the tidal volume is equal to the average of the total amount of inhalation of the previous five breaths, and the current total amount of inhalation is set to 0.

[0091] As a further optional embodiment, the respiratory rate and the inspiration-expiration ratio are determined by the following steps:

[0092] Determine whether the current breathing state is an inhalation state or an exhalation state according to the current gas flow information;

[0093] When the current breathing state is the inhalation state, the current inhalation time is determined according to the gas flow information, and the current total inhalation time is determined according to the sum of the current inhalation time and the total amount of the previous inhalation time;

[0094] When the current breathing state is the exhalation state, the current exhalation time is determined according to the gas flow information, and the current total exhalation time is determined according to the sum of the current exhalation time and the total exhalation time of the previous time;

[0095] When the current breathing state changes from the inhalation state to the exhalation state, the inhalation-exhalation ratio is determined according to the quotient of the current total inhalation time and the current total exhalation time, the average breathing time is determined according to the current total inhalation time, the current total exhalation time and the current number of breaths, and then the breathing frequency is determined according to the average breathing time, and the current total inhalation time, the current total exhalation time and the current number of breaths are set to 0.

[0096] Specifically, each time the timer interrupt is entered, if the current state is in the inhalation state and there is no change in the breathing state, the total amount of inhalation time is calculated, that is, the total amount of inhalation time = this inhalation time + the total amount of the previous inhalation time, and the current inhalation time = 1 / sampling rate; the total amount of exhalation time is calculated in the same way. If the current breathing state is converted from inhalation to exhalation, the breathing frequency = 60s / the average of the previous five breaths (total exhalation time + total inhalation time), and then the current total exhalation time is set to 0. The ratio of inhalation time to exhalation time is the inhalation-exhalation ratio.

[0097] As an optional implementation, leakage compensation is performed on the tidal volume according to the airway pressure information to obtain the real tidal volume, which specifically includes:

[0098] Obtaining a leakage flow-airway pressure mapping table pre-calibrated by experiments;

[0099] According to the airway pressure information, query the leakage flow-airway pressure mapping table to obtain the current leakage flow;

[0100] The true tidal volume is determined by the sum of the current leak flow and the tidal volume.

[0101] Specifically, since there is an exhaust port at the end of the ventilator mask, the flow rate flowing through the ventilator pipeline is not equal to the flow rate of the human respiratory pipeline, so leakage compensation is required. Since the caliber area is very small, the leak port on the nasal mask can be regarded as a throttle port. When the gas parameters (default is atmospheric pressure), temperature and molar gas constant at the low-pressure end are fixed, the mass flow rate flowing through the throttle port is only related to the equivalent cross-sectional area of ​​the throttle port and the gas parameters at the high-pressure end. When the same model of respiratory mask is used for testing, the leakage flow rate is only related to the pressure inside the tube. Seal the breathing port at the mask end, leaving only the exhaust port for ventilation, manually adjust the pressure size (start 0: step 0.5: end 20), and take the average of 50 sets of flow data at each pressure. The leakage flow-pressure formula uses cubic fitting, which represents the relationship between the leakage flow rate and the pressure inside the tube when the caliber area is fixed (i.e., a specific model of respiratory mask), which helps to improve the accuracy of pipeline gas flow measurement, thereby improving the measurement accuracy of tidal volume.

[0102] The present invention uses advanced Kalman filtering technology to perform real-time fusion processing on data from different sensors, effectively reducing measurement noise and uncertainty. This method dynamically adjusts the filtering parameters to adapt to the physiological changes and environmental conditions of different patients, thereby improving the accuracy of monitoring data and the stability of the system. Specifically, this technology is applied as follows:

[0103] Enhanced accuracy and reliability: By integrating data from different sensors (such as pressure sensors, flow sensors, oxygen concentration sensors, etc.), the measurement accuracy of gas parameters can be improved. Each sensor may produce different readings due to environmental factors or its own errors. Data fusion can effectively reduce these errors and obtain more reliable output.

[0104] Fault detection and early warning: This data fusion algorithm can identify anomalies in sensor readings and detect possible faults in advance. For example, if the output of a sensor is significantly different from the readings of other sensors, the system can issue an alarm to prompt maintenance personnel to check.

[0105] As an optional implementation, the ventilator output gas monitoring method further includes a low ventilation warning step, which specifically includes:

[0106] Determine a first maximum airflow value and a first minimum airflow value within a preset time period according to the gas flow information, and determine a basic tidal volume according to a difference between the first maximum airflow value and the first minimum airflow value;

[0107] Determine a second maximum airflow value and a second minimum airflow value for the current period according to the gas flow information, and determine a current tidal volume according to a difference between the second maximum airflow value and the second minimum airflow value;

[0108] When the current tidal volume is less than 30% of the basic tidal volume, a low ventilation alarm is issued.

[0109] As an optional embodiment, the ventilator output gas monitoring method further includes the following steps:

[0110] Obtain the user's blood oxygen saturation and heart rate through the blood oxygen and heart rate monitoring module;

[0111] When the blood oxygen saturation is lower than a preset first threshold for a preset number of times monitored within a preset breathing cycle, a hypoglycemia alarm is issued.

[0112] Specifically, the intelligent reminder function of this solution automatically generates alarm or reminder information by analyzing monitoring data in real time. For example, when low ventilation or low blood oxygen level is detected, the system will issue an alarm through the circuit board LED light or buzzer to promptly notify medical staff or patients to make adjustments. This function can greatly improve the timeliness and effectiveness of nursing care.

[0113] Hypoventilation alarm: Hypoventilation / obstruction events can be judged by long-term reduction in nasal airflow or tidal volume (or almost no) during sleep. When implementing positive pressure ventilation therapy, the flow in the ventilator pipeline includes the superposition of the user's spontaneous breathing flow and the ventilator support gas flow. When there is no breathing action or respiratory obstruction occurs, the ventilator will still provide support gas to maintain positive pressure ventilation. Therefore, the algorithm in the ventilator can use tidal volume to judge respiratory events. If the tidal volume is less than 30% of the tidal volume of the previous few respiratory cycles, it can be judged as a hypoventilation / obstruction event. After stable breathing, the maximum airflow value within 30s minus the minimum airflow value is calculated to approximate the basic tidal volume (this calculation does not require the determination of the respiratory cycle, and the algorithm is simple and robust), which is used as the standard for judging respiratory events. The current tidal volume is detected with a 10-second sliding window. If the tidal volume (maximum flow value-minimum flow value) within these 10 seconds is detected to be less than 30% of the basic tidal volume, a hypoventilation / obstruction event is considered to have occurred. Since the tidal volume fluctuates greatly during a night's sleep even if no respiratory events occur, affected by sleep states such as sleep phase, the basic tidal volume is updated every 30 seconds. Under spontaneous breathing, after a period of normal breathing, if a period of more than 10 seconds of breathing with a tidal volume less than 30% of the basic tidal volume is detected, it is a hypoventilation event, and the hypoventilation alarm light is on.

[0114] Hypoxic alarm: Under spontaneous breathing, after a period of normal breathing, if the blood oxygen value is monitored to be lower than 94% for two consecutive times, the hypoxic alarm light will turn on.

[0115] The method steps of the embodiment of the present invention are described above. It can be recognized that the embodiment of the present invention obtains airway pressure information, gas flow information and oxygen concentration information of the breathing duct gas, determines the tidal volume, respiratory rate and inspiratory-expiratory ratio according to the gas flow information, performs leakage compensation on the tidal volume according to the airway pressure information, obtains the real tidal volume, displays the airway pressure information, inspiratory-expiratory ratio, real tidal volume, respiratory rate and oxygen concentration information, and improves the comprehensiveness and accuracy of the ventilator output gas monitoring.

[0116] In addition, the present invention adopts an innovative detachable modular design, allowing users to quickly replace sensor modules according to specific needs. Each module follows a unified interface standard, ensuring plug-and-play and automatic software recognition and configuration. This design not only improves the adaptability and flexibility of the equipment, but also reduces the cost of maintenance and upgrades. Specifically, the detachability of the sensor is achieved through plug-in connectors or quick-connect components; intelligent recognition functions are added to the modules, such as using digital interfaces or smart sensors, which can automatically identify the connected modules and adjust the system settings. The advantages of this design are as follows:

[0117] 1) Enhanced adaptability: Different application scenarios may require different monitoring functions. For example, medical monitoring may require more accurate oxygen concentration measurement, while industrial applications may focus on flow and pressure monitoring. The modular design allows users to quickly replace sensors or control modules according to specific needs.

[0118] 2) Convenient maintenance and upgrade: The modular design makes equipment maintenance easier, and faulty components can be quickly replaced without disassembling the entire device. This reduces maintenance costs and reduces downtime. In addition, as technology advances, users can easily upgrade sensors or control modules to achieve better performance.

[0119] 3) Personalized customization: Different users may have different monitoring needs, and the modular design allows customized configuration. Users can choose the most suitable sensor according to their specific needs to improve the user experience.

[0120] 4) Reduce production costs: Modular design breaks down products into standardized components, allowing each component to be produced and replaced independently, thereby simplifying the production process, improving production efficiency, and ultimately reducing costs.

[0121] Reference Figure 4 , an embodiment of the present invention provides a ventilator output gas monitoring system, comprising:

[0122] An information acquisition module, used to obtain airway pressure information, gas flow information and oxygen concentration information of the breathing duct gas;

[0123] An information processing module, used for determining tidal volume, respiratory rate and inspiration-expiration ratio according to gas flow information;

[0124] A leakage compensation module is used to perform leakage compensation on the tidal volume according to the airway pressure information to obtain the real tidal volume;

[0125] The information display module is used to display airway pressure information, inspiration-expiration ratio, true tidal volume, respiratory rate and oxygen concentration information.

[0126] The contents of the above method embodiments are all applicable to the present system embodiments. The functions specifically implemented by the present system embodiments are the same as those of the above method embodiments, and the beneficial effects achieved are also the same as those achieved by the above method embodiments.

[0127] Reference Figure 5 , an embodiment of the present invention provides a ventilator output gas monitoring device, comprising:

[0128] at least one processor;

[0129] at least one memory for storing at least one program;

[0130] When the at least one program is executed by the at least one processor, the at least one processor implements the above-mentioned method for monitoring ventilator output gas.

[0131] The contents of the above method embodiments are all applicable to the present device embodiments. The functions specifically implemented by the present device embodiments are the same as those of the above method embodiments, and the beneficial effects achieved are also the same as those achieved by the above method embodiments.

[0132] An embodiment of the present invention further provides a computer-readable storage medium, in which a program executable by a processor is stored. When the program executable by the processor is executed by the processor, it is used to execute the above-mentioned ventilator output gas monitoring method.

[0133] A computer-readable storage medium according to an embodiment of the present invention can execute a ventilator output gas monitoring method provided by an embodiment of the present invention, can execute any combination of implementation steps of the method embodiment, and has the corresponding functions and beneficial effects of the method.

[0134] The embodiment of the present invention also discloses a computer program product or a computer program, wherein the computer program product or the computer program includes computer instructions, and the computer instructions are stored in a computer-readable storage medium. A processor of a computer device can read the computer instructions from the computer-readable storage medium, and the processor executes the computer instructions, so that the computer device executes Figure 1 The method shown.

[0135] In some selectable embodiments, the function / operation mentioned in the block diagram may not occur in the order mentioned in the operation diagram. For example, depending on the function / operation involved, the two boxes shown in succession can actually be executed substantially simultaneously or the above-mentioned boxes can sometimes be executed in reverse order. In addition, the embodiment presented and described in the flow chart of the present invention is provided by way of example, for the purpose of providing a more comprehensive understanding of technology. The disclosed method is not limited to the operation and logic flow presented herein. Selectable embodiments are expected, wherein the order of various operations is changed and the sub-operation of a part for which is described as a larger operation is performed independently.

[0136] In addition, although the present invention is described in the context of functional modules, it should be understood that, unless otherwise specified to the contrary, one or more of the above-mentioned functions and / or features can be integrated into a single physical device and / or software module, or one or more functions and / or features can be implemented in a separate physical device or software module. It is also understood that a detailed discussion of the actual implementation of each module is unnecessary for understanding the present invention. More specifically, in view of the properties, functions and internal relationships of the various functional modules in the device disclosed herein, the actual implementation of the module will be understood within the conventional skills of the engineer. Therefore, those skilled in the art can implement the present invention set forth in the claims without excessive experimentation using ordinary techniques. It is also understood that the specific concepts disclosed are merely illustrative and are not intended to limit the scope of the present invention, which is determined by the full scope of the appended claims and their equivalents.

[0137] If the above functions are implemented in the form of software functional units and sold or used as independent products, they can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of the present invention, or the part that contributes to the prior art or the part of the technical solution, can be embodied in the form of a software product. The computer software product is stored in a storage medium, including several instructions for a computer device (which can be a personal computer, a server, or a network device, etc.) to perform all or part of the steps of the above methods of each embodiment of the present invention. The aforementioned storage medium includes: U disk, mobile hard disk, read-only memory (ROM, Read-Only Memory), random access memory (RAM, Random Access Memory), disk or optical disk and other media that can store program codes.

[0138] The logic and / or steps represented in the flowchart or otherwise described herein, for example, can be considered as an ordered list of executable instructions for implementing logical functions, and can be embodied in any computer-readable medium for use by an instruction execution system, device or apparatus (such as a computer-based system, a system including a processor, or other system that can fetch instructions from an instruction execution system, device or apparatus and execute instructions), or in conjunction with such instruction execution systems, devices or apparatuses. For the purposes of this specification, "computer-readable medium" can be any device that can contain, store, communicate, propagate or transmit a program for use by an instruction execution system, device or apparatus, or in conjunction with such instruction execution systems, devices or apparatuses.

[0139] More specific examples of computer-readable media (a non-exhaustive list) include the following: an electrical connection with one or more wires (electronic device), a portable computer disk case (magnetic device), a random access memory (RAM), a read-only memory (ROM), an erasable and editable read-only memory (EPROM or flash memory), an optical fiber device, and a portable compact disk read-only memory (CDROM). In addition, the computer-readable medium may even be a paper or other suitable medium on which the above-mentioned program is printed, since the above-mentioned program can be obtained electronically, for example, by optically scanning the paper or other medium, followed by editing, deciphering or processing in other suitable ways as necessary, and then stored in a computer memory.

[0140] It should be understood that the various parts of the present invention can be implemented by hardware, software, firmware or a combination thereof. In the above-mentioned embodiments, a plurality of steps or methods can be implemented by software or firmware stored in a memory and executed by a suitable instruction execution system. For example, if implemented by hardware, as in another embodiment, it can be implemented by any one of the following technologies known in the art or their combination: a discrete logic circuit having a logic gate circuit for implementing a logic function for a data signal, a dedicated integrated circuit having a suitable combination of logic gate circuits, a programmable gate array (PGA), a field programmable gate array (FPGA), etc.

[0141] In the above description of this specification, the description with reference to the terms "one embodiment / example", "another embodiment / example" or "certain embodiments / examples" etc. means that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic representation of the above terms does not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described may be combined in any one or more embodiments or examples in a suitable manner.

[0142] Although embodiments of the present invention have been shown and described, it will be appreciated by those skilled in the art that various changes, modifications, substitutions and variations may be made to the embodiments without departing from the principles and spirit of the present invention, and that the scope of the present invention is defined by the claims and their equivalents.

[0143] The above is a specific description of the preferred implementation of the present invention, but the present invention is not limited to the above embodiments. Those skilled in the art may make various equivalent modifications or substitutions without violating the spirit of the present invention. These equivalent modifications or substitutions are all included in the scope defined by the claims of this application.

Claims

1. A method for monitoring the output gas of a ventilator, characterized in that: The following steps are involved: Obtaining airway pressure information, gas flow information and oxygen concentration information of the breathing tube gas; Determine tidal volume, respiratory rate and inspiration-expiration ratio according to the gas flow information; Performing leakage compensation on the tidal volume according to the airway pressure information to obtain a real tidal volume; The airway pressure information, the inspiration-expiration ratio, the real tidal volume, the respiratory rate and the oxygen concentration information are displayed.

2. A method for monitoring ventilator output gas according to claim 1, characterized in that: The step of obtaining airway pressure information, gas flow information, and oxygen concentration information of the breathing duct gas specifically includes: Acquiring the airway pressure information of the breathing duct gas through a pressure sensor arranged in the breathing duct; Acquiring the gas flow information of the gas in the breathing duct by means of a differential pressure flow sensor arranged in the breathing duct; The oxygen concentration information of the breathing duct gas is obtained through an oxygen sensor arranged in the breathing duct.

3. A method for monitoring ventilator output gas according to claim 1, characterized in that: The tidal volume is determined by the following steps: Determine whether the current breathing state is an inhalation state or an exhalation state according to the current gas flow information; When the current breathing state is the inhalation state, the current inhalation volume is determined according to the gas flow information, and the current inhalation total volume is determined according to the sum of the current inhalation volume and the previous inhalation total volume; When the current breathing state changes from the inhalation state to the exhalation state, the tidal volume is determined according to the quotient of the current inhalation total volume and the current breathing number, and the current inhalation total volume and the current breathing number are set to 0.

4. A method for monitoring ventilator output gas according to claim 1, characterized in that: The respiratory rate and the inspiration-expiration ratio are determined by the following steps: Determine whether the current breathing state is an inhalation state or an exhalation state according to the current gas flow information; When the current breathing state is the inhalation state, the current inhalation time is determined according to the gas flow information, and the current total inhalation time is determined according to the sum of the current inhalation time and the total amount of the previous inhalation time; When the current breathing state is the exhalation state, the current exhalation time is determined according to the gas flow information, and the current total exhalation time is determined according to the sum of the current exhalation time and the total exhalation time of the previous time; When the current breathing state changes from an inhalation state to an exhalation state, the inhalation-exhalation ratio is determined according to the quotient of the current total inhalation time and the current total exhalation time, the average breathing time is determined according to the current total inhalation time, the current total exhalation time and the current number of breaths, and then the breathing frequency is determined according to the average breathing time, and the current total inhalation time, the current total exhalation time and the current number of breaths are set to 0.

5. A method for monitoring output gas of a ventilator according to claim 1, characterized in that: The step of performing leakage compensation on the tidal volume according to the airway pressure information to obtain a real tidal volume specifically includes: Obtaining a leakage flow-airway pressure mapping table pre-calibrated by experiments; According to the airway pressure information, query the air leakage flow-airway pressure mapping table to obtain the current air leakage flow; The actual tidal volume is determined according to the sum of the current leakage flow and the tidal volume.

6. A method for monitoring ventilator output gas according to claim 1, characterized in that: The ventilator output gas monitoring method also includes a low ventilation early warning step, which specifically includes: Determine a first maximum airflow value and a first minimum airflow value within a preset time period according to the gas flow information, and determine a basic tidal volume according to a difference between the first maximum airflow value and the first minimum airflow value; determining a second maximum airflow value and a second minimum airflow value of a current period according to the gas flow information, and determining a current tidal volume according to a difference between the second maximum airflow value and the second minimum airflow value; When the current tidal volume is less than 30 percent of the basic tidal volume, a low ventilation alarm is issued.

7. A method for monitoring output gas of a ventilator according to any one of claims 1 to 6, characterized in that: The ventilator output gas monitoring method also includes the following steps: Obtain the user's blood oxygen saturation and heart rate through the blood oxygen and heart rate monitoring module; When the blood oxygen saturation is detected to be lower than a preset first threshold for a preset number of times within a preset breathing cycle, a hypoglycemia alarm is issued.

8. A ventilator output gas monitoring system, characterized in that: include: An information acquisition module, used to obtain airway pressure information, gas flow information and oxygen concentration information of the breathing duct gas; An information processing module, used to determine tidal volume, respiratory rate and inspiration-expiration ratio according to the gas flow information; A leakage compensation module, used for performing leakage compensation on the tidal volume according to the airway pressure information to obtain a real tidal volume; An information display module is used to display the airway pressure information, the inspiration-expiration ratio, the real tidal volume, the respiratory rate and the oxygen concentration information.

9. A ventilator output gas monitoring device, characterized in that: include: at least one processor; at least one memory for storing at least one program; When the at least one program is executed by the at least one processor, the at least one processor implements a ventilator output gas monitoring method as described in any one of claims 1 to 7.

10. A computer-readable storage medium storing a program executable by a processor, characterized in that: The processor-executable program is used to perform a ventilator output gas monitoring method as claimed in any one of claims 1 to 7 when executed by the processor.

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